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A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating

A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current

A61B18/1206—Generators therefor

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating

A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current

A61B18/14—Probes or electrodes therefor

A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets

A61B17/32—Surgical cutting instruments

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets

A61B2017/00017—Electrical control of surgical instruments

A61B2017/00022—Sensing or detecting at the treatment site

A61B2017/00026—Conductivity or impedance, e.g. of tissue

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets

A61B2017/00017—Electrical control of surgical instruments

A61B2017/00022—Sensing or detecting at the treatment site

A61B2017/00084—Temperature

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets

A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for

A61B2017/22097—Valve removal in veins

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets

A61B17/42—Gynaecological or obstetrical instruments or methods

A61B2017/4233—Operations on Fallopian tubes, e.g. sterilization

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00053—Mechanical features of the instrument of device

A61B2018/00107—Coatings on the energy applicator

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00053—Mechanical features of the instrument of device

A61B2018/00107—Coatings on the energy applicator

A61B2018/00119—Coatings on the energy applicator with metal oxide nitride

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00684—Sensing and controlling the application of energy using lookup tables

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00696—Controlled or regulated parameters

A61B2018/00702—Power or energy

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00696—Controlled or regulated parameters

A61B2018/00761—Duration

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00779—Power or energy

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00791—Temperature

A61B2018/00803—Temperature with temperature prediction

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00827—Current

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00869—Phase

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00875—Resistance or impedance

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00886—Duration

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00636—Sensing and controlling the application of energy

A61B2018/00773—Sensed parameters

A61B2018/00892—Voltage

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B2018/00982—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body combined with or comprising means for visual or photographic inspections inside the body, e.g. endoscopes

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body

A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating

A61B2018/044—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating the surgical action being effected by a circulating hot fluid

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges

A61B90/06—Measuring instruments not otherwise provided for

A61B2090/064—Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension

Abstract

A minimally-invasive surgery apparatus (10) for causing the lumen of a vein to collapse to prevent blood flow through the vein, e.g., a varicose vein or a side branch of the saphenous vein, includes an electrode (20) which is electrically connected to a power source (14), and the electrode (20) is percutaneously advanced into the vein. Then, the power source (14) is activated to energize the electrode (20) and thus the blood vein until the blood vein sufficiently collapses to block the lumen of the vein.A feedback loop including a microprocessor (44) is also provided for sensing electrical impedance of the tissue within the vein being energized and for deenergizing the electrode (20) when the impedance reaches a predetermined value. The apparatus (10) can also be used to block a fallopian tube.

Description

~ W0 95119148 2 1 ~ t 4 5 3 r~ 74 APPARATUS AND METHOD FOR VENOUS Ll(~ATIONThe present application claims priority from U.S. Patent application serial number 08/183,994, filed January, 18, 1994, for an inYention entitled "Apparatus and Method For Venous Ligation", assigned to the same assignee as the present mvention, and from U.S.Patentapplicationserialnumber08/2~5,932,fi1edMarch22, 1994,foraninventionentitled "Method For Tubal Electro-Ligation", assigned to the same assignee as the present invention. FIELD ~DF TI~E INVENTIONThe present invention relates generally to surgical tools. More particularly, the present mvention relates to apparatus and methods for closing body vessels. The present invention particularly, though not exclusively, relates to t l~ lul;V_.iul~ of Fallopian tubes. F"~ QuNDCertain surgical treatments require the ' ~ or removal of blood veins from the body. For example, the treatmellt of varicose veins sometimes requires the varicose veins to be removed from the bod~ in am mvasive, painful, slu.. ! ' v, amd time-consuming procedure. Also, the saphenous vein is surgically modifled during a procedure, known as in situ saphenous vem bypass, for alleviating conditions caused by reduced blood flow through an occluded femoral artery.In situ saphenous vem bypass is a procedure in which the saphenous vein m a h= leg, which normally returns vt:nous blood from the ankle upwardly through the leg, is ' to the femoral artery at an upstream (proxrmal) location on the artery amd a downstream (distal) location on the altery to assume the function of the femoral artery, i.e., to deliver arterial blood to the leg.~ Such a bypass procedure may be required when the femoral artery has become too occluded or otherwise impaired between the upstream and du.. l. locations to transport the flow of blood required of it.When the saphenous vem is to assume the function of the femoral artery, it becomes necessary to close off, i.e., to ligato, so called "side bramch~ blood verns. These side branch veins are generally smaller thm the saphenous vein and are colloquially known as "tributaries" when they lead to the saphenous vem and "~L~ ul~" when they lead to deeper venous circulation. Side brarches ordinarily establish pathways for venous blood mto the saphenous vein for returning the blood to the heart and lungs. Accordingly, to prevent the unwanted flow of arterial blood directly into the venous system via the saphenous vern, the side branches ;md perforators must be ligated. Stated drfferently, by ligating the side br;mches, arterial blaod which is permitted to flow through the saphenous Wo95119148 P~l/lJ..,','~ '74 vein and thereby bypass the occluded segment of the artery is prevented from invading the venous system through the side branches.Typically, side branches are ligated by constricting the side branches with sutures.U r ' ' ~ ligating side branches with sutures cam be trme-consuming and labor-ir~tensive, because all the side bramches must be located either by rnaking a large number of small incisions in the leg or by making orle very large incision. Also, it is difficult to ligate side branches with sutures in ~ procedures, i.e.,; ' I '1~,.As recognized by the present invention, side branches of the saphenous vein may be ligated in less invasive procedures. More particularly, the present inver~tion recognizes that blood flow through side branches of tbe saphenous vein can be quickly and easily stopped by advarlcing an electrode into the side br_nch and er~ergizing the electrode to cause the tissue to coagulate and thereby block fluid flow through the side branch. As further recognized by the present invention, varicose veins cam be quickly and easily treated by ligating the n in less invasive procedures. Thereby, unsightly ~ in the leg attributable to varicose veins can be elrmirlated in an out-patient procedure.Although coagulating devices have been rntroduced for other surgical arrli~tinn~these devices typically have bulky components which are designed for use within a relatively large body cavity that h s been exposed by surgery. ~ " existrng coagulating devices camlot easily be used to stop blood flow from "hard-to-reach" sources, such as sapherlous vein side branches. r~.L}..,....ul~, existrng coagulating devices cannot easily be used rn 1~ , surgery for the treatrnent of varicose veirls.Moreover, many coagulating devices fimction simply by applying electricity to tissue. The length of time the tissue is e~posed to the electricity is controlled by the surgeon, usually by depressing a foot pedal linked to a source of electricity, e.g., a Bovie model generator made by Valley Labs of Colorado. Consequently, tissue can easily be ".~ overheated, thereby causnng unwanted scabbnng, charring, amd other unnecessary tissue datnage. Such damage can be particularly onerous in certain , , e.g., saphenous venn side bramch ligation and varicose venn treatment.Indeed, excessive electro-ligation of varicose ven~s nn an attempt to reduce ~u caused by the veills may be a cure that is worse th;m the disease. Stated differently, applying rf energy to a blood venn over excessive tnme periods or at excessively high power can result in arcing and perforation of venn.It is therefore am object of the present invention to provide a device that can less-nnvasively ligate side branches of a saphenous venn. Another object of the present mvention is to provide am apparatus and method for less nnvasive treatment of varicose ven~s. Still ~ Wog~1191~8 21 8 1 4 53 r~llu~r~7~

arlother object of the present invention is to provide an apparatus and method for less invasive surgical ligation which is easy to use and cost-effective to r . SUMIUAR~ OF 1~, INVENTIONA device for use in endoscopic surgery to inhibit blood flow through a blood vessel includes an elongated electrical con~luctor which has a distal end. Preferably, the conductor includes a segment that is bendable into a IJlc '~ ' shape, and a direction indicator may be provided for indicating the direction in which the conductor is bent.A source of electricity is electrically coimected to electrical conductor. As interlded by the presently preferred ' " t, the source of electricity generates m rf output sufficient to cause the blood vessel to collapse and insufficient to perforate the blood vessel.Also, an electrically insulative smooth flexible sheath surrounds at least a segment of the conductor. In accordanoe with the present invention, the sheath has an outside diameter of less than one millnmeter (Imm) to permit easily slidably engaging the sheath with the lu~nen of the blood vessel.An electrode is co~mected to the distal end of the electrical conductor such t~t the source of electricity cart be energized to energize the electrode to thereby cause the lumen of the blood vessel to collapse wh~ n the electrode is positioned in the vessel. In one preseMly preferred ~ l t, the electrode extends beyond a distal end of the sheath, and the length of the electrode is ~I~Vl~ / equal to the diameter of the blood vessel.Ad~ v~l~, the electrode is folmed nntegrally with the conductor, and the electrode includes a roumded distal tip. Furtller, the electrode preferably includes ,m anti-sticking coating which is deposited on the electrode.Preferably, a feedback device is provided for sensmg a preselected parameter of the blood vessel. Tlte feedback device generates a signal when the preselected parameter reaches a ,v.c ' ' value, and the preselected parameter is affected by the treahment of the preselected portion of tissue. The preselected parameter can be r~r~r~mr~, in which case the feedback device mcludes a temperature sensor secured to the apparatus for sensrng the temperature of the electrode.Alternatively, the preselected parameter is at least one electrical parameter selected from the group of parameters consistnlg of: source of electricity ouhput voltage, time rate of change of source of electricity output voltage, source of elechicity ouhput power, time rate of change of source of electricity ouhput power, source of electricity ouhput current, time rate of change of source of elechicity output curreM, tissue dechical mlpedmce, time rate of change of tissue electrical mu,)edance.

218t453 Wo95/19148 P~llu..,~ 74 In another aspect of the preseM inveMion, an apparatus which is connectable to apower source for electrically ligating a preselected portion of lissue includes an electrically insulative sheath configured for slidably engaging a lumen of a body vessel. Additionally, the apparatus mcludes an electrode which is positioned in the sheath. As intended by the present inveMion, the electrode is electrically connectable to the power source for energizing the preselected portion of tissue when the electrode is positioned adjaoent the preselected portion of tissue and the power source is activated to provide power to the electrode. Afeedback device is provided for sensing a preselected parameter and for generating a signal IC~ L,~ of the magnitude of the preselected parameter. In accordance with the present invention, the preselected parameter is affected when the preselected portion of tissue is energized by the electrode.In still another aspect of tbe present rnvention, a method is disclosed for treating a varicose vein. The method includes the steps of providing an electrically energizable electrode, and then ~ , advancrng the electrode into the varicose vein such thatthe electrode is juxtaposed with the wall of the varicose vern. Next, coMact is established between the wall of the varicose vern and the electrode, and the electrode is energized until the vein collapses around the electrode to thereby block blood flow through the vein.In yet another aspect of the present rnvention, a method is disclosed for electro-ligation of a blood vessel. The method rncludes the steps of providing an electrically energizable electrode and an endoscopic instrument, and disposing the electrode in the instrument. Then, the instrument is I l~ advanoed with electrode into the blood vessel, and the electrode is energized until the vessel collapses around the electrode to thereby block blood flow through the vein.In amother aspect of the preserlt invention, a method is disclosed for dectro-ligation of a fallopian tube. The method includes the steps of providing an electrically energizable electrode and an instrument, and disposing the electrode in the instrument. Then, the instrumeM is advanced with electrode into the fallopian tube, amd the electrode is energized until the tnbe collapses around the electrode to thereby block the fallopian tube.The details of the present mvention, both as to its construction and operation, can best be understood in reference to the ~ drawings, in which like numerals refer to like parts, and which: BRI13 F L~ ON OF T~ DRAVVINGSFigure 1 is a perspective view of the apparatus for venous ligation of the present invention;

Wo 9511914~ 74 Figure 2 is a cross-sectional view of the apparatus for venous ligalion of the present invention, as seen along the line 2 2 in Figure 1;Figure 3 is a block diagraln of the electrical components of the apparatus shown in Figure l;Figure 4 is a block diagran1 of the O~IU~ UI logic for generating the control signal; amd Figure S is a schematic view of the apparatus of the present invention with portions broken away, shown in conjunction with a woman's fallopian tube for blockmg the tube. DETAILED DESCRIPTION OF TE33E ~r r r~ EMR~Referrmg initially to Figure 1, an endoscopic dectro-cauterizer for closing off side branches of blood veins and for l)locking blood flow through varicose veirls is shown, generally designated 10. While thl discussion below focusses on side branch closure and varicose vein treatment, it is to be understood that the principles of the present invention disclosed below can be applied to a wide variety of medical treatments requirmg tissue mcluding perforator ~ein treatment, hemorrhoid treatment, amd ll~ IU~lL~ Llrrlir~rinnc As shown in Figure 1, the cauterizer 10 mcludes a probe 11 amd a connector body 12. The connector 12 is preferably a standard banana plug conmector, and can be conmected to a source 14 of electrical po~ver via an electrical line 16. The source 14 c;m.~u~ be a Bovie generator made by Valley T ' of Colorado.It is to be understood that the probe 11 can be I '~ advanced rnto a blood vessel, e.g., a varicose vem, or that it could be engaged with the lumen of am endoscopic surgerv instrument 13, and then the instrument 13 with probe 11 advanced into, e.g., the side branch of a saphenous vem. As intended by the present mvention, the irlstrument 13 can be any one of the iDstruments disclosed in the followmg U.S. patent Al ~ " , all of which are assigned to tbe sole owner of the assignee of the praent mvention: serial number 07/867, 841, filed April 13, 1992 for an mvention entitled ~FLEXIBLE TIPCATHETER"; serialnumberO7/9~4,120, filedSeptember29, 1992foranmventionentitled "FLEXIBLE ENDOSCOPE WITH ~l Y~u ~ ACTIVATING WlRE n; and serial number 07/970,402, filed November 2, 1992 for am invention entitled ~ENDOSCOPE FOR SHUNTPLACEMENT", all of which are , ' herem by reference.In cross-reference to Figur~s 1 and 2, the probe 11 mcludes an dongated electrical conductor 18 havmg a ~ "~ r~d electrode 20 formed mtegrally on the distal end of the conductor 18. Preferably, the conductor 18 has am electrical resistance below ten ohms per foot (10S~/h). In the pre~'erred ' t, ~e conductor 18 with electrode 20 wo 95/19148 2 1 8 1 4 5 3 P ~ 7~ --is made of type 304 stainless steel. By, - - -, r-, l " " ,~ the electrode 20 integrally with the conductor 18, ' ~, costs of the probe 11 are minimized, and a firm commection is established between the electrode 20 and the conductor 18.Figure 2 shows that the conductor 18 has an outside diameter ODC, of about eighteen thousandths of an inch (.018"). Also, the conductor 18 tapers radially inwardly to a bendable segment 22 having an outside diameter ODC~ of about ten thousandths of an inch (.010"). As the skilled artisam will appreciate, the bendable segment 22 is malleable and flexible. t'~ , 'y, the segment 22 c~m be bent into a ~ ' ' curvilinear shape, as shown in Figure 1, to facilitate advancing the probe 11 imto a side b~anch and to facilitate contact between the electrode 20 and the wall of a varicose vein into which the probe 11 has been advanced.As shown best in Figure 2, the electrode 20 is formed with a rounded distal tip 24.An abutment surface 26 is established by the electrode 20, and the abutment surface 26 radially projects beyond the conductor 18. Preferably, the electrode 20 has an outer diameter ODI of between about twenty eight thousamdths of an inch and eighty four thousandths of an inch (.028"-.084"), and more preferably the outer diameter OD, is about seven-tenths of a millimeter (0.7mm).The length L of the electrode 20 is between about one to ten millimeters (I-lOmm).Specifically, the length L is established to be a~ equal to the maximum diameterof the blood vein into which the probe 11 is advanced. More specifically, for blood veins having a diameter of about four to six millimeters (~ ' ), the length L of the electrode 20 is about four millimeters (4mm). Also, for blood veins havmg a diameter of about six to eight millimeters (f '` ), the length L is about six millimeters (6mm).Further, for blood veins having a diameter larger than eight millimeters (8mm), the length L is about eight millimeters (8mm).In the presently preferred ~ ' " t, a non-sticking, non-insulative substance 28 is deposited on the surface of the electrode 20 to inhibit sticking of the electrode 20 to body tissue during energization of the dectrode 20. Preferably, the substance 28 is chronne which is deposited on the electrode 20 by vapor deposition. Alternatively, the electrode 20 c~m be coated with titamiuln nitrate or Teflon~.Figure 2 also shows that an insulative sheath 30 surrounds the conductor 18 and abuts the abutment surface 26 of the electrode 20. As can be seen im Figure 2, the outer surface of the sheath 30 is flush with the outer surface of the electrode 20. In accordance with the present invention, the sheath 30 is bonded to the conductor 18 with a high-temperature epoxy.

~ W095119148 2 1 8 1 453 P~ '7~

As intended by the preserlt invention, the sheath 30 is made of an electrically resistive, smooth, ! . ' ' ' material, such as PEBAX0 made by Atochem, Inc. of New Jersey, or TFE Teflon0, which typically has a dielectric strength of about seven hundred to one thousand volts per mil of material (700-1000 v/mil). Also, the sheath 30 is made of a material which will not easily melt or breakdown under the high ~ that are tyoically generated during eL,.,ll, y. Further, the sheath 30 should be made of a material that has a low coefficient of friction, PeBax0 is the presently preferred materlal of choice for the sheath 30 in light of its above-mentioned attributes and because it is relatively flexible, elastlc, and has a low coefficient of friction. These attributes permit the sheath 30 to be easily advamced through a potentially curvilinear, small-dianleter lumen of blood vein or an endoscopic instrument.Further to this end, the outside diameter OD of the sheath 30 (and, hence, the outside diameter of the probe 11~ is preferably equal to less than about one millimeter (Imm). In one presently preferred ~ ' " t, the outside diameter OD of the sheath 30 is between about twenty eight thousandths of .~n mch and ninety two thousandths of an inch (.028"-.092"). Alternative materials whirh can be used for the sheath 30 include polyimide, ,~,ly~lyl~.lr, attd ~uly~ Jyl~If desired, a sensor 32 (Figlre 1) can be attached to the electrode 20. The sensor 32 can be a i- .', thermistor, or other suitable temperature-sensmg device.Alternatively, the sensor 32 can be a pressure sensor for sensing fluid pressure at ~he distal end of the probe 11. Figure 2 shows that a flat, generally ~ ' bend indicator 34 is bonded to the sheath 30. As shown, the indicator 34 is formed with a projecting edge 36 that is dist;mced from the sheath 30. As mtended by the present mvention, the bend indicator 34 is orierlted during ~ _ such that the projectmg edge 36 extends outwardly in the same direction as ~he bend of the bendable segment 22 of the conductor 18. The indicator 34 remains outside the patient's body durirlg surgery, and the operator of the cauterizer 10 can . l~, ascertain during surgery the direction m which the bendable segment 22 of the conductor 18 has been bent.Figure 2 shows tbat the bend indicator 34 is formed integrally with a metal jacket 37, and the jacket 31 surrounds the sheath 30 to traosmit torque to the probe 11. An insert 38 made of silicone rubber is dispo!;ed between the jacket 37 and sheath 30. Further, the probe 11 has a proximal end 39, and a high voltage line, including a high voltage lead 40 amd high volhge insulator 41, abuts the proximal end 39 of the probe 11. A wire 42 is soldered to the high voltage lead 40 amd conductor 18 to further erlsure electrical corltact Wo 95/19148 ~ 2 1 8 1 4 5 3 F~~ 74 between Ihe two components. It is to be appreciated that the high voltage lead 40 in turn is electricaily connected to the source 14 of electricity via the line 16 and plug 12 (Figure 1).in the operation of the cauterizer 10, reference is made to Figures 1 and 2. Theplug 12 is electrically conmected to the source 14 of electricity. Thus, both the sensor 32 and electrode 20 of the probe 11 are electrically comnected to the source 14 of electricity.The source 14 cam be electricaily conmected to a IIII~IU,UIU~.~,DDUI 44 which isV~ a type "486" u,ulu~a~ul. As disclosed more fuily below, the ' U~UIU~.~D~UI 44 is electricaily comnected to the source 14, and the IIIII,IU,UIU~.CDDUI 44 generates a control signai for controlling the source 14 in response to, inter alia, signais from the sensor 32. If desired, indicators 45 can be provided for displaying cauterizer 10 voltage, current, impedamce, temperature, and other parameters, in accord~mce with the operation of the cauterizer 10 disclosed below.Next, for side branch electro-ligation, the probe 11 is advamced into the woricing channel lumen of the instrument 13. Then, the instrument 13 into which the probe 11 has been advamced is itself advanced into the blood vein of a patient. The electrode 20 of the probe 11 can be selectively advanced out of the lumen in which it is slidably disposed, and the source 14 of electricity activated to electro-ligate a iocaiized portion of tissue. The probe 11 is then retracted from the vein of the patient. As rntended by the present mvention, the power level of the source 14 is sufficient to cause the veim to collapse, but insufficient to perforate the vein. To this end, when the source 14 is a Bovie model generator, the so-cailed "cut" waveform (i.e., a 500KHz sinusoidai rf signai) setting is used.Aiternatively, for varicose vein treatment, the probe 11 itself is ~advanced into the vein, amd the wail of the vein is maruaily urged agan st the electrode 20.Then, the electrode 20 is energized to cause the wail of the vein to ~ , collapse mwardly, thereby blocking blood flow through the vein. The electrode 20 is then retrieved from the vein.It is to be understood that while the cauterizer 10 disclosed above is a monopolar device, it m4y aiso be a bi-polar device, e.g., the cauterizer 10 c;m have electrodes configured like those disclosed in co-pending U.S. patent application seriai no. 08/054,123, filed April 26, 1993, for am imvention entitled "Bi-Polar r~ , assigned to thesole owner of the present invention and , ' herem by reference.Now referrmg to Figure 3, the electricai components of the cauterizer 10 can be seen. As shown, the sensor 32 is connected to ~m anaiog-to-digitai ("A/Dn) converter 48, for converting the anaiog temperature signai from the sensor 32 mto a digitized signai . The 2181~53 ~ WO 95/19148 P~l/u., ~ 74 _g A/D converter 48 can adv ,, '~ be a type AD578û4P converter ma~ie by Burr Brown,or some other suitable converter krlown in the art.Figure 3 further shows that the A/D converter 48 is connected to a noise filter 50.The noise filter 50 cam be a hardware or, more preferably, software filter which filters noise from the digitized signal from the sensor 32. For example, the filter 50 can be ~to discriminate against sixty Hert:~ (60 Hz) or fifty Hertz (50 Hz) noise from nearby electrical wlllr The fiiter 50 can also be ~l~ ,, ' to average a ,Ult,l' ' number (e.g., ten) of consecutive signals from the sensor 32 and output a signalIc~ lhLive of the aveMge, or the filter 50 can be a low-pass filter. When the noise filter 50 is a software filter, it can function by averaging a pluMlity (e.g., ten) of sensor signals in accordance with means well-kno~wn in the art.Also, the fliter 50 can be u,,, ,, ' to block a signal from the sensor 32 which greatly varies from the immediatel~ previous signal. A great variance from one signal to the next may indicate an erroneous or spurious signal level. In other woriis, if a first signal from the sensor indicates an electrode 20 temperature of, e.g., eighty degrees centigrade (80C), and a second signal that is immediately temporally after the first indicates an electrode 20 temperature which varies by more tban a l,r~ ' ' amount (e.g., 10C) from the first signal, the filter 50 b~locks the second signal from further processimg. Tbe hardware i . if any, of bi~th the A/D converter 48 and the noise filter 50 cam be housed in the cauterizer 10 or so~rce 14. When the filter 50 is a software filter, the software filter 50 c;m be part of the Ut~.U.~ UI 44.Figure 3 also shows that a timer 52 is provided which monitors the length of time the source 14 energizes the electrode 20. Tbe timer 52 generatQ a signal IC,U.~ , of the length of time of electrode 20 alergization and sends this signal to the 44. When the length of time exceeiis a ~ ' time period, e.g., a time period between about ten seconds and foriy seconds (10 sec- 40 sec), the . 44 causQthe source 14 to stop energizing the electrode 20.Additionally, components are provided for measuring the output voltage and current of tbe source 14 of electricity, and for providing signals ICI~lQ~.~ALi. ., ûf tbe ûutput vûltage, current, power, and impedance (and, hence, the voltage, current, power, and tissue impedance at tbe tip of tbe dectrode 20) to the I i_lU~ .Q~Ul 44. More specificaily, a component 54, e.g., a current sensin~ transformer or resistor, is comnected in seriQ between the source 14 of electricity and the electrode 20, and a current rectifier filter ("RIF~) 56 satnples the voltage upstream and downstream of the component 54. Accordingly, the Wo 95/19148 2 1 8 1 4 5 3 r.l,.m - -74 current RIF 56 outputs a signal l~ulca~ , of the output current of the source 14 of electricity.Aiso, a Yoltage sampling R/F 58 is provided for generating a signal l~/lC~of the output voltage of the source 14 of electricity. A~iv ~ " both the current amd voltage R/Fs 56, 58 can be full wave diode rectifiers with associated filtering capacitors conmected in a 5" well-imown in the art.Figure 3 shows that the current and voltage R/Fs 56, 58 are respectively connected to A/D converters 60, 62, each of which is ~ , sirnilar to the temperature A/Dconverter 48. In turn, both A/D converters 60, 62 are connected to the Illi~,lUIJlU~ Ul 44.Still referring to Figure 3, the l...~.lU~llUI~ UI 44 generates an output control signai and sends the control signai to am electricai buffer 64. The buffer 64 is any suitable device which essentiaily isolates the u,ulu~vl 44 from the source 14 of electricity, and which provides correct driving signais to the source 14.The output signal from the buffer 64 is sent to the source 14 of electricity to control the output power of the source 14 of electricity. To do this, the control signal can be used to vary the output voltage of the source 14 of electricity, or the modulation of the signai from the source 14 of electricity, by means well-icnown in the art. For example, the signal from the buffer 64 can be used as the bias signai to a power trarlsistor (not shown) that is part of the output circuitry of the source 14 of electricity. Consequently, as the signai from the buffer 64 changes, the bias of the transistor changes to change the output of the source 14 of electricity.Now referrmg to Figure 4, the details of the operation of the , U~ VI 44 cam be seen. The UIJ.U~UI 44 commences a sampiing cycle at begm circle 100. From the circle 100, the Ul~lUl,L,~UI proceeds to block 1û2, wherein a software coumter "T"is set equal to zerû. Then at block 104, "T" is set equal to T + 1. If, at block 104, Tequals a ~1~ ' ' software counter "T,", the UylU-,~ u. 44 stops, i.e., e~its theroutme shown in Figure 4.Otherwise, the ' Ul~IU~ UI 44 proceeds in parallel to decision blocks 106, 108, ar~dll0,andtoblocksll2arldll4. AtdecisionblockslO6,108,110,the U,UIU~UI44 retrieves from memory and then respectively compares source 14 of electricity output voltage (Vb). electrode 20 temperatnre (Tb), and source 14 of electricity output current ab) to rcspective I ' ' voltage,; , , arld current setpoints Vl, Tl, Il. If either Vb or Tb exceeds its I ' ' setpoint, or if Ib falls below its Isetpoint, the ,~ 44 generates a control sigrlal to cause the source 14 of WO 95/~9148 r~ -~u_,5,'C ~ '7 -Il-electriciy to stop energizing the electrode 20. Otherwise. the lUI.lU,UlUoe~DUl 44 proceeds to blocks 116, 118.At block 112, on the other hand, the IlU IU~UIUvv~UI 44 calculates the impedanoe(Zb) of the tissue adjacent the electrode 20 by dividing Vb by Ib. Then, the UIJlU~v~DUl 44 mûves to decision block 120, where the u,uluv~.æv. 44 compares Zb to a ,UI~ " ' setpoint mlpedance Zl. If Zb exceeds Z1, poor electrical cormection or i oor placement of the electrode 20 may be indicate~. In such a case, the U,UI~ 44 generates a control signal to caus~ the souroe 14 of electricity to stop energizirlV the electrode 20. As intendd by the present invention, the source 14 of electricity is deenergized before Zb reaches zero (0). Else, the U,UIV-~VI 44 procoeds to blockæ 122 and 124. In the presently preferred; ' - ~, Zl is set equal to about fifty ohms.It is to be understood that while overall impedance is used in the presently preferrd ~:mhorl~m~nt the phase difference between Vb and Ib can be measurd for deter~nining the capacitive impedance component and resistive i~mpdance component, and then either impdance component can be usd in lieu of or in addition to Zb- Inded, the phase difference between Vb and Ib c,m be used as am input to the UlJIU~:~UI 44 m lieu of or in addition to the parameters discussed above.Likewise, at block 114, the u~,.u.v~aul 44 calculates the output power (Pb) ofthe source 14 of electricity by multiillying Vb and Ib. Therl, the u~", 44 moves to decision block 126, where the 1 44 compares Pb to a ~ ' ' setpoint power Pl. If Pb exoeds Pl, the UllLlUI/lU~ vl 44 generates a control signal to cause the souroe 14 of electricity to stop energizmg the electrode 20. Otherwise, the U~llU~44 proceeds to return block 127, and thence back to block 104.At blocks 116 and 118, the u i~lUIJl Uv~vl 44 respectively caiculates the differenoe between Vb, Ib, and Vb ~. Ib ~ to yield ~V, ~1, where Vb 1, Ib ~, are the respective voltage and current vaiues caicuiated in the immvdiately precding cycle. AiternatiYely, Vb " Ib, can be averages of the n precdmg u,l- r ' v vaiues where n= any integer, e.g., ten (10), three (3), etc.From blocks 116, 118, the ~ u - ~ 44 moves to respective decision blocks 130, 132. At block 130, the ' u~u~, 44 compares ~V to a I ' ' voltage difference, i.e., ~Vz. If ~V exoeeds ~V2, the ul,,u.v,~u, 44 moves to block 134,wherein the u~lu.va~u, 44 generates a control signal tû cause the source 14 of eiectricity to deactivate or to rduce its power output by a I ' ' increment ~P, e.g., by two watts to fûur watts (2w4~w). Otherwise, ti~e , ~ 44 moves to block 127 and thence back to block 104 for another cycle, -WO95119148 ~ 1 8 1 4 53 1~ 74 Likewise, at block 132, the ~ uulu~,-a~ui 44 compares ~I to a ~UICI' ' current difference, i.e., ~12. If ~1 exceeds ~12, the u,ulu~,~"aul 44 movoe to block 134, wherein the Ul!IU-,~Ul 44 generates a control signal to cause tbe source 14 oi electricity to reduce its power output by QP. Otherwise, the U,UIU~ UI 44 moves to block 127 and thence to block 104 for another cycle.Recall that at block 120 the Illi~lU~llU~ Ul 44 compared Zb to a ~ ' ' constant m~pedance setpoint Z1. As shown in Figure 4 starting at block læ, the lUil.lUUlU-,~UI 44 also compares Zb to a variable rmpedance setpoint Z2 which is patient-dependent.More specifically, at block 122 the Illil,lU,UlU~.,.JI 44 sets an entermg argument variable Z3 equal tû Zb if T equals a I ' ' stabilization trme period T2.Otherwise, the entering argument variable Z3 is set equal to itself. More specifically, when T<T2, Z3 is set equal to a relatively low default value. When T=T2, Z3 is set equal to Zb. and when T > T2, Z3 remains equal to the value of Zb set at T=T2. Thus, the entering argument Z3 is patient-dependent. In the preferred ' ' t, T2 equals between about two (2) seconds to ten (10) seconds, and the default value of Z3 is equal to about two humdred ohms (200n).Then, the U,UIUI C~UI 44 moves to block 135, wherein the UIVIU.,~ UI 44 retrieves a lulc ' ' ' rmpedance limit Z2 by accessmg a data table amd using Z3 as the enterrng argument. A IC,UlC~ , table is provided herein as Table 1. From block 135, the U,UIUI.~UI 44 moves to decision block 136, wherein Zb is compared to Z2. If Zb exceeds Z2, the UAUIU~ UI 44 moves to block 134 to reduce source 14 of electricity output power or deenergi~e the electrode 20 altogether, and thence to block 128 to generate a tone l~lc,cil.iaii.., of Zb~ Otherwise, the U,UIU~ UI 44 moves drrectly to block 128 to generate a tone IC,Ull,~iaii~. of Zb' It is to be understood that while block 128 in Figure 4 rndicates that a tone ICUl.,.~l. aii~.. of inlpedance is generated, the tone or other tones could be generated which are l~UlC~;lliali~ ., of the other parameters discussed herem.From block 128, the ' U,UIU.,~UI 44 ves to block 127 arld then returns to block 104.The skilled artisan will appreciate that the operation of the ~ ,lu~lv~ ul 44 atblock 122 erlsures that the entermg argument variable Z3 is set equal to a relatively stabili2ed Zb- More particularly, for a brief n~itial stabilization period (T2), power interruption is avoided when minor transients in rmpedamce (Zb) might occur amd otherwise cause the L..~IU,UlU~ul 44 to deenergize the source 14 of electricity. Stated differently, the U,UI- 44 reduces source 14 output power during the stabilization trme T2 only . . .

~ WO 9~/19148 2 ~ 8 1 4 5 3 r~ 74 in the instance when Zb is less than the initial default value of Z2, which is acco}dingly set eo,ual to a relatively low (e.g., eight hundred ohms (800S~)) value.On the other hand, after th~ stabilization period T2 elapses, Zb can be e~pected to reach a steady state value while tlie tissue surrounding the probe 11 is treated by the electrode 36. During this treatment period, the entering argument Z3 is defined to be equal to the value of Zb at time T=T2, and the table look-up of Z2 is thus , ' ' usinga patient-dependent eMering argument Z3.From block 124, the U~JIU~ DUI 44 proceeds to decision block 138, wherein the l~..uy.u~,aDu. 44 compares Qi' to a yl, ' ' impedance difference, i.e., QZ4.1f QZ exceeds QZ4, the UIJIU~,~,D~UI 44 moves to block 134, wheNin the , J~aul 44 generates a control signal to cause the source 14 of electricity to reduce its power output by QP, and thence to block 127. Otllerwise, the ~ luylu~ ,. 44 moves directly to block 127, and thence to block IC4 for another cycle.Thus, at blocks 130, 132, 134 the l~ lU~LUC~DDul 44 determines whether the time rate of change of Vb, Ib, or Zb are e.~cessive, and if so, the UylU~vl 44 reduces the output power of the source 14 of elec tricity, or deenergizes the electrode 20 altogether The present invention also envisions calculating the time rate of change of temperature Tb in a like manner and reducing the output power of the source 14 of electricity in respoDse to an excessively rapid increæe hn Tb or in the time rate of change of Tb. The present invention ,' the above-disclosed operation of the UylU~,~DVI 44 because, as reco,~nzed by the present invention, the tissue ir~pedance at the tip of the elxtrode 20, and thl: temperature of the tip of the electrode 20, is affected by the ~ of the tissue irrlmediately adjacent the electrode 20.More particularly, when the tissue has not yet been cauterized, the impedance at the electrode 20 tip is relatively low. 1n contrast, when the tissue has just undergone - , the impedbnce at the electrode 20 ~ip is relatively high. Thus, the output voltage, current, and impedance o~ the source 14 of electricity are all affected by the of tissue adjacent the electrode 20. Stated differently, the magnitudes of the output voltage and current of the source 14 of electricity, and the Dlaglntude of the impedance of the tissue adjacent the electr~de 20, are dependent upon the body 1 -- ~ ~- ;~1; ~ of the patient. Likewise, the temperature (Tb) of the ele~trode 20 tip also depends in part upon the ~ of the tissue adjacent the tip of the dectrode 20.Hence, by ".~ controlling the output of the source 14 of electricity based upon any one of or a combination of Zb. Ib. Vb. Pb. ancl Tb (and their respective tilne derivatives), the present invention ensures that tissue acljacent the venous wall is not .. _ _ _ _ _ _ _ _ _ _ . _ .... ..... ....... _ _ . .....

2 1 8 1 453 P~ 74 damaged any further than necessary to effect Also, by precisely controlling the OUIpUt of the source 14 of electricity, the present invention erlsurQ that tissue is precisely cauterked as appropriate for side branch/varicose vein closure. Aiternatively, by automatically generating a tone IC~UIC~C...4~ of any one of or a combination of Zb. Ib. Vb.Pb, and Tb and their respective trme derivatives, the present rnvention enablQ tile surgeon to precisely control the source 14.It is to be fmther understood that the present invention ,' Qstablishing power-dependent ~JIC' ' ' ' setpoints, i.e., setpornts that vary with the rnanuaily-Qtablished power setting of the source 14 of electricity. Thus, Vl, Il, Zl, Z2, Z3, Pl, Tl, amd ~Z4 cam ail vary with the power settrng of the source 14 of electricity. In such an t, a data table correlating power setting with I ' ' setpoints is stored rn the electronic memory of the u~lu-,Qaul 44 for look-up by the VUIU~,Q~UI 44 at the appropriate decision blocics discussed above.Figure 5 shows that a probe 200 which in ail essential rQpects is identical to the probe 11 shown in Figure I can be advanced into a woman's failopian tube 202. More specifically, the probe 11 can be advanced through the vaginai opening 204 of the woman's uterus 206 and into one of the woman's failopian tubes. Then, the probe 200 can be energized as discussed above to cause a wail portion 208 of the faiiopian tnbe 202 wilich is juxtaposed with the probe 200 to collapse around the probe 200. Thereby, the failopian tube 202 is ' "~ blocked by electro-iigation to prevent passage of human ,c,u,u~ cells through the tube 202.While the particular method for tubal electro-ligation as herern shown and described in detaii is fully capable of attaining the above-described ûbjects of the rnvention, it is to be understood that it is the prQentiy preferred embodrment of the prQent invention and is thus IC~UIQC~ of the subject matter which is broadly . ' ' by the prQeM rnvention, that the scope of the prQent invention fully; . other . ' " which may become obvious to those sicilled in the art, and that the scope of the prQent invention is accordrngly to be limited by nothing other than the appended clarms.

WO 95/19148 ~1814 5 3 r~ 74 Z3(01~ns~

Claims (26)

1. A device for use in endoscopic surgery to inhibit blood flow through a blood vessel, comprising:an elongated electrical conductor having a distal end;a source of electricity electrically connected to electrical conductor;an electrically insulative smooth flexible sheath surrounding at least a segment of the conductor, the sheath having an outside diameter of less than one millimeter (Imm) to permit easily slidably engaging the sheath with the lumen of the blood vessel; and an electrode connected to the distal end of the electrical conductor such that the source of electricity can be energized to energize the electrode to thereby cause the lumen of the blood vessel to collapse when the electrode is positioned in the vessel.

2. The device of Claim 1, further comprising a feedback device for sensing a preselected parameter of the blood vessel and for generating a signal when the preselected parameter reaches a predetermined value, wherein the preselected parameter is affected by the preselected portion of tissue.

3. The device of Claim 1, wherein the electrode extends beyond a distal end of the sheath, and the length of the electrode is approximately equal to the diameter of the blood vessel.

4. The device of Claim 2, wherein the preselected parameter is temperature, and the feedback device includes a temperature sensor secured to the apparatus for sensing the temperature of the electrode.

5. The device of Claim 2, wherein the preselected parameter is at least one electrical parameter selected from the group of parameters consisting of: source of electricity output voltage, time rate of change of source of electricity output voltage, source of electricity output current, tune rate of change of source of electricity output current, source of electricity output power, time rate of change of source of electricity output power, tissue electrical impedance, time rate of change of tissue electrical impedance.

6. The device of Claim 5, wherein the preselected parameter is impedance.

7. The device of Claim 6, wherein the electrode is formed integrally with the conductor, and the electrode includes a rounded distal tip.

8. The device of Claim 7, further comprising an anti-sticking coating deposited on the electrode.

9. The device of Claim 8, wherein the conductor includes a segment bendable into a predetermined shape.

10. The device of Claim 9, further comprising a direction indicator for indicating the predetermined shape.

11. The device of Claim 10, wherein the source of electricity generates an rf output sufficient to cause the blood vessel to collapse and insufficient to perforate the blood vessel.

12. An apparatus connectable to a power source for electrically ligating a preselected portion of tissue, comprising:an electrically insulative sheath configured for slidably engaging a lumen of a body vessel;an electrode positioned in the sheath, the electrode being electrically connectable to the power source for energizing the preselected portion of tissue when the electrode is positioned adjacent the preselected portion of tissue and the power source is activated to provide power to the electrode; and a feedback device for sensing a preselected parameter and for generating a signal representative of the magnitude of the preselected parameter, wherein the preselected parameter is affected when the preselected portion of tissue is energized by the electrode.

14. The apparatus of Claim 13, wherein the electrode is advanceable into a blood vein, and the length of the electrode is approximately equal to the diameter of the blood vein.

15. The apparatus of Claim 14, further comprising an electrical conductor formed integrally with the electrode and connected to the power source, the electrode including a rounded distal tip and an anti-sticking coating deposited on the electrode.

16. The apparatus of Claim 15, wherein the output of the power supply is reduced when the signal representative of the magnitude of the preselected parameter reaches a predetermined value.

17. A method for treating a varicose vein, comprising the steps of: (a) providing am electrically energizable electrode; (b) percutaneously advancing the electrode into the varicose vein such that the electrode is juxtaposed with the wall of the varicose vein; (c) establishing contact between the wall of the varicose vein and the electrode; and (d) energizing the electrode until the vein collapses around the electrode to thereby block blood flow through the vein.

18. The method of Claim 17, wherein the electrode is energized by a power supply, and the method further comprises the step of determining the electrical impedance of the tissue adjacent the electrode.

19. The method of Claim 16, further comprising the step of automatically reducing of the electrode when the impedance equals a predetermined value.

20. The method of Claim 19, wherein the energizing step is without perforating the vein.

21. A method for electro-ligation of a blood vessel, comprising the steps of:(a) providing an electrically energizable electrode and an endoscopic instrument; (b) disposing the electrode in the instrument; (c) percutaneously advancing the instrument with electrode into the blood vessel; and (d) energizing the electrode until the vessel collapses around the electrode to thereby block blood flow through the vein.

22. The method of Claim 21, wherein the energizing step is accomplished without perforating the vein.

23. A method for ligating a fallopian tube, comprising the steps of:(a) providing an electrically energizable electrode;(b) advancing the electrode into the fallopian tube such that the electrode is juxtaposed with the wall of the fallopian tube;(c) establishing contact between the wall of the fallopian tube and the electrode; and (d) energizing the electrode until the fallopian tube collapses around the electrode to thereby block the fallopian tube.

24. The method of Claim 23, wherein the electrode is energized by a power supply, and the method further comprises the step of determining the electrical impedance of the tissue adjacent the electrode.

25. The method of Claim 24, further comprising the step of automatically reducing energization of the electrode when the impedance equals a predetermined value.

26. The method of Claim 25, wherein the energizing step is accomplished without perforating the fallopian tube.